JP2018201742A - Ophthalmologic imaging apparatus - Google Patents

Abstract

To provide an ophthalmologic imaging apparatus capable of acquiring a favorable tomogram in a fundus oculi of a subject's eye.SOLUTION: The ophthalmologic imaging apparatus includes: change means changing a profile of measurement light in an OCT optical system; and acquisition means that applies the measurement light to a subject's eye in a state where the profile of the measurement light is changed by the change means into a plurality of mutually-different first profiles and acquires first OCT data thereof. The change means changes the profile of the measurement light into a new second profile different from the first profiles as a profile for the imaging, on the basis of the plurality of OCT data acquired by the acquisition means. The acquisition means applies the measurement light to the subject's eye with the profile changed into the second profile and acquires second OCT data.SELECTED DRAWING: Figure 1

Description

  The present disclosure relates to an ophthalmologic photographing apparatus that photographs a tomographic image of an eye to be examined.

  As an ophthalmologic photographing apparatus for photographing a tomographic image of an eye to be examined, an optical coherence tomography (OCT) using low coherent light is known (see Patent Document 1).

JP 2008-29467 A

  An optical tomographic interferometer (OCT device) divides light emitted from a light source into measurement light and reference light, and irradiates the subject's eye (for example, the fundus) with the divided measurement light. However, the measurement light applied to the subject's eye is sometimes obstructed by cloudiness or edema caused by eyelids of the subject's eye or diseases such as cataracts, and a good tomographic image may not be obtained.

  In view of the above prior art, it is an object of the present disclosure to provide an ophthalmologic photographing apparatus that can acquire a good tomographic image on the fundus of the eye to be examined.

  In order to solve the above problems, the present disclosure is characterized by having the following configuration.

(1) An ophthalmologic imaging apparatus according to a first aspect of the present disclosure includes an OCT optical system that detects an OCT signal based on measurement light and reference light irradiated on an eye to be examined, and processes the OCT signal to thereby examine the eye to be examined. An ophthalmic imaging apparatus for acquiring the OCT data of the OCT optical system, wherein the measuring light profile in the OCT optical system is changed, and the measuring light profile is changed to a plurality of different first profiles by the changing means. An acquisition means for irradiating the eye to be examined with the measurement light and acquiring the first OCT data, and the changing means is based on the plurality of OCT data acquired by the acquisition means. The profile of the measurement light is changed to a new second profile that is different from the first profile as a profile for the actual photographing, and the acquisition is performed. The means irradiates the eye to be examined with the measurement light in a state where the second profile is changed, and acquires second OCT data.
(2) The ophthalmologic imaging method according to the second aspect of the present disclosure includes an OCT optical system that detects an OCT signal based on measurement light and reference light irradiated on the eye to be examined, and processes the OCT signal to thereby examine the eye to be examined. In the ophthalmic imaging method for acquiring the OCT data, the measuring light profile is changed to a plurality of first profiles different from each other by the changing means for changing the measuring light profile in the OCT optical system. Based on the first acquisition step of irradiating the eye to be examined with the measurement light and acquiring the respective first OCT data and the plurality of OCT data acquired by the acquisition means, the profile of the measurement light is obtained as a profile for main imaging. A change step for changing the profile to a new second profile different from the first profile; and a change to the second profile. And a second acquisition step of irradiating the eye with the measurement light and acquiring second OCT data.

1 is an external configuration diagram of an ophthalmologic photographing apparatus according to an embodiment. It is a schematic block diagram which shows the optical system and control system of the ophthalmologic imaging device which concerns on a present Example, Comprising: The optical arrangement | positioning at the time of fundus photography is shown. It is a schematic block diagram which shows the optical system and control system of the ophthalmologic imaging device which concerns on a present Example, Comprising: The optical arrangement | positioning at the time of anterior eye part imaging | photography is shown. It is a figure which expands and shows a scanning part. It is a flowchart explaining control operation. It is a figure which shows the anterior eye part observation image of a to-be-examined eye. It is a figure explaining DMD. It is a figure which shows the relationship between DMD and a 1st profile. It is a figure explaining the transmittance | permeability distribution. It is a figure explaining a 2nd profile. It is a figure which shows the example of a change in the optical system of an ophthalmologic imaging device.

<Overview>
Hereinafter, one exemplary embodiment will be described with reference to the drawings. 1 to 10 are diagrams for explaining an ophthalmologic photographing apparatus according to the present embodiment. In this embodiment, the horizontal direction of the eye to be examined is described as the X direction, the vertical direction as the Y direction, and the axial direction as the Z direction. The surface direction of the fundus may be considered as the XY direction. In addition, the items classified by <> below can be used independently or in association with each other.

  In addition, this indication is not limited to the apparatus described in a present Example. For example, terminal control software (program) that performs the functions of the following embodiments is supplied to a system or apparatus via a network or various storage media, and the system or apparatus control device (for example, CPU) reads the program. It is also possible to execute.

  For example, the ophthalmic imaging apparatus (for example, the ophthalmic imaging apparatus 1) in the present embodiment has an OCT optical system (for example, the OCT optical system 2), and acquires OCT data of the eye to be examined by processing the OCT signal. For example, the OCT optical system (OCT device) may have Fourier domain optical coherence tomography (FD-OCT) as a basic configuration. For example, as the FD-OCT, spectral domain OCT (SD-OCT) or wavelength sweep type OCT (SS-OCT) may be used. Further, for example, the OCT device may have time domain OCT (TD-OCT) as a basic configuration. Note that, for example, the technique of the present disclosure is based on the standard OCT for detecting the reflection intensity of the test object, the OCT angiography (for example, Doppler OCT) for detecting the motion contrast data of the test object, and the polarization-sensitive OCT ( It may be applied in PS-OCT (Polarization Sensitive OCT) or the like. Further, the present invention may be applied to a multi-function OCT in which standard OCT and PS-OCT are combined.

<OCT optical system>
For example, the OCT optical system detects an OCT signal by measurement light and reference light irradiated on the eye to be examined. For example, the OCT optical system may include a configuration related to an interferometer for obtaining a tomographic image of a test object using the OCT principle. For example, the OCT optical system includes a light source (for example, light source 11), a splitter (for example, coupler 15), a combiner (for example, coupler 15), a detector (for example, detector 40), a reference optical system (for example). For example, a reference optical system 30) may be provided.

  For example, the splitter may split light from the light source into measurement light and reference light. For example, the combiner may combine (interfere) the measurement light and the reference light. For example, a divider and a combiner may be combined. For example, a divider and a combiner may be provided separately. For example, any of a beam splitter, a half mirror, a fiber coupler, a circulator, and the like may be used for the splitter and the combiner. For example, the detector may receive interference signal light generated by interference between the measurement light and the reference light. For example, the reference optical system may include a configuration for causing the reference light to travel in the apparatus and interfere with the measurement light.

  For example, the OCT optical system acquires OCT data of the eye to be examined by processing an OCT signal. Note that the OCT optical system switches the depth zone of the eye to be imaged, the first position corresponding to the first depth zone of the eye to be examined (for example, the anterior segment of the eye to be examined), and the second depth zone of the eye to be examined. The OCT data may be acquired at the second position corresponding to (for example, the fundus of the eye to be examined).

<Measurement optical system>
For example, the measurement optical system (for example, the measurement optical system 20) may be configured to guide the measurement light to the eye to be examined. For example, the measurement optical system may include a scanning unit (optical scanner) (for example, the scanning unit 24). For example, the scanning unit scans the measurement light on the first position corresponding to the first depth zone of the eye to be examined. Further, for example, the scanning unit scans the measurement light on the second position corresponding to the second depth zone of the eye to be examined. For example, the scanning unit may include two optical scanners (for example, a galvano mirror 241 and a galvano mirror 242) that deflect measurement light in different directions. For example, a reflection scanner such as a MEMS scanner, a resonant scanner, a polygon mirror, or an acoustooptic device may be used as the optical scanner included in the scanning unit. That is, the optical scanner included in the scanning unit may be any scanner that can deflect the measurement light.

<OCT data>
For example, the OCT data includes tomographic image data indicating the reflection intensity characteristics of the eye to be examined, OCT angio image data (for example, OCT motion contrast image data) of the eye to be examined, Doppler OCT image data indicating the Doppler characteristics of the eye to be examined, It may be at least one of polarization characteristic image data indicating the polarization characteristic. Each data may be generated image data, or may be signal data before an image is generated.

  For example, the tomographic image data may be A-scan tomographic image data. For example, the tomographic image data may be B-scan tomographic image data. For example, the B-scan tomographic image data is tomographic image data acquired by scanning the measurement light in any of the XY directions (for example, the X direction) along the scanning line (transverse position). Also good. For example, the tomographic image data may be three-dimensional tomographic image data. For example, the three-dimensional tomographic image data may be tomographic image data acquired by two-dimensionally scanning the measurement light. For example, OCT data includes OCT front (Enface) image data acquired from three-dimensional tomographic image data (for example, an integrated image integrated in the depth direction, an integrated value of spectrum data at each XY position, a certain depth). Luminance data at each XY position in the vertical direction, retina surface layer image, etc.).

  For example, the OCT angio image data may be two-dimensional OCT angio image data. For example, the two-dimensional OCT angio image data is OCT angio image data acquired by scanning the measurement light in any of the XY directions (for example, the X direction) along the scanning line (transverse position). There may be. Further, for example, the OCT angio image data may be three-dimensional OCT angio image data. Note that, for example, the three-dimensional OCT angio image data may be OCT angio image data acquired by two-dimensionally scanning the measurement light. Further, for example, the OCT angio image data may be front (En face) motion contrast data acquired from three-dimensional motion contrast data.

  For example, the ophthalmologic photographing apparatus according to the present embodiment includes a changing unit (for example, DMD 28) that changes the profile of the measurement light in the OCT optical system. For example, the changing unit can change the profile of the measurement light to a plurality of different first profiles (for example, the first profile 100). For example, the measurement light profile may be changed to at least two or more first profiles.

  For example, the first profile changes the distribution of measurement light. For example, as the distribution of the measurement light, among the measurement light emitted toward the fundus of the subject's eye, any part of the subject eye (for example, the pupil plane (pupil surface of the subject's eye) of the path from the anterior segment to the fundus ), The distribution of measurement light in a vitreous body, etc.). The distribution of the measurement light may be one that changes the measurement light into a regular pattern shape. In this case, the first profile may have a shape such as a lattice pattern or a stripe pattern, a ring shape, or a shape obtained by enlarging or reducing the measurement light. The distribution of the measurement light may be one that changes the measurement light into an irregular pattern shape. For example, the first profile may have a predetermined pattern shape in which -1 of the Walsh-Hadamard basis is a region where the measurement light is irradiated to the eye, and +1 is a region where the measurement light is not irradiated to the eye. It may be a random pattern shape.

  In addition, for example, the ophthalmologic imaging apparatus according to the present embodiment irradiates the eye to be measured with the measurement light in a state in which the measurement light profile is changed to a plurality of different first profiles by the changing unit, and acquires each first OCT data. Acquisition means (for example, the control unit 70). With such a configuration, the examiner tries a plurality of first profiles, and until the return light of the measurement light irradiated on the subject's eye reaches the fundus and is again collected by the OCT optical system. Information on which path the measurement light has propagated can be obtained.

  For example, the changing means in this embodiment is a DMD (Digital Micromirror Device). As a result, the profile of the measurement light can be easily changed to various shapes. In addition, as a change means, the structure which can change the profile of measurement light should just be provided. For example, in this case, a configuration in which at least one of a transmissive LCD (Liquid Crystal Display), a reflective LCD, a wavefront modulation element, etc., is used as the changing means in addition to the DMD. For example, when DMD is used as the changing means, only discrete binary values of irradiation and non-irradiation can be obtained in the profile of the measurement light, but continuous values can be obtained when using an LCD or a wavefront modulation element. Is possible. Thereby, for example, the first profile can be changed to a pattern shape such as a (discrete) cosine basis.

<Change measurement light profile>
For example, the changing unit uses a new second profile (for example, the second profile 200) as a profile for main imaging based on a plurality of OCT data acquired by the acquiring unit. ). The second profile has a measurement light distribution different from the measurement light distribution in the first profile. That is, the second profile is changed to a pattern shape completely different from the first profile by the changing means.

  For example, the acquisition unit irradiates the eye under measurement with the measurement light profile changed to the second profile, and acquires the second OCT data. At this time, the changing unit may change the second profile so that the measurement light profile can collect (receive) more return light of the measurement light irradiated to the eye to be examined. For example, such a second profile may be changed to a profile in which the return light of the measurement light is equal to or higher than a predetermined threshold (for example, 80%, 90%, etc.). Note that the predetermined threshold value may be acquired in advance by experiments or simulations. Of course, the predetermined threshold value may be set to an arbitrary value. As a result, the examiner can change the second profile to an optimum profile for the eye to be examined with reference to the first profile, and can acquire highly accurate OCT data.

  For example, the changing unit changes the second profile by creating a transmittance distribution (for example, a transmittance distribution 85) of the return light of the measurement light for the eye E from the plurality of OCT data acquired by the acquiring unit. May be. For example, the transmittance distribution may be any as long as it is easy to transmit the return light of the measurement light on the pupil of the eye to be examined. The transmittance distribution may be signal data or image data obtained by imaging the signal data. For example, as such a transmittance distribution, the ease of transmission of the return light of the measurement light may be displayed as a map.

  For example, the transmittance distribution may be created based on a predetermined signal intensity of the first OCT data. For example, as the signal strength, the total amount of the OCT signal may be detected. In this case, a value obtained by integrating the envelope of the OCT signal may be detected as the total amount. Further, for example, the predetermined signal intensity may be obtained by integrating absolute values in a part of the wavelength region or part of the frequency region of the first OCT data. Alternatively, the predetermined signal intensity may be a feature amount such as a peak, contrast, or histogram. Thereby, for example, even when the signal is saturated, it becomes easy to detect a difference for each first profile. Alternatively, in consideration of the movement of the eye to be examined, evidence of reflection from the same location may be obtained by a known segmentation process.

  For example, the transmittance distribution may be created based on the luminance value in the OCT image. In this case, the rise or fall of the luminance in any one of the XYZ directions may be detected. In this case, the luminance value may be detected for each pixel of the OCT image.

  Note that the changing means may be configured to determine the strength at a predetermined signal strength of the plurality of OCT data acquired by the acquiring means. For example, the changing unit determines the strength of the signal strength by determining whether or not the detected predetermined signal strength exceeds a predetermined threshold value. For example, the predetermined threshold value used for the determination process may be acquired in advance by experiments or simulations.

  For example, the ophthalmologic photographing apparatus according to the present embodiment is one of the paths from the anterior segment to the fundus out of the measurement light emitted toward the fundus of the subject's eye in a state where the plurality of first profiles are changed to each other. There may be provided a light amount adjusting means (for example, the control unit 70) for making the light amount of the measurement light in the subject eye portion equal. For example, the ophthalmologic photographing apparatus may have a configuration in which only the first profile having the same amount of measurement light is stored in the storage unit (for example, the memory 72). In this case, the light amount adjusting means may set the stored first profiles in order, so that the light amounts of the measurement light irradiated to the eye to be examined are the same. Further, for example, the ophthalmologic photographing apparatus may have a configuration in which a first profile having the same amount of measurement light and a first profile having a different amount of measurement light are mixedly stored in the storage unit. . In this case, the light amount adjusting means may select and sequentially set the first profile having the same light amount of the measurement light from the first profiles.

  For example, the light amount adjusting means may adjust the total amount of the measurement light at any part of the eye to be examined in the path from the anterior segment to the fundus when adjusting the amount of the measurement light to be the same. Good. For example, the light amount adjusting unit may be configured to adjust the light amount of the measurement light to be the same by controlling the changing unit so that the irradiation area of the measurement light on the eye to be examined is the same. Further, for example, the light amount adjusting means may be configured to adjust the light amount of the measurement light to the same by controlling the output of the light source. Further, for example, the light amount adjusting means may be configured to adjust the light amount of the measurement light to the same by controlling a member arranged in the optical path of the measurement light, or the member is inserted into and removed from the optical path of the measurement light. By doing so, the configuration may be such that the amount of measurement light is adjusted to be the same. For example, as such a member, a density filter, a polarizing filter, a neutral density filter, or the like may be used. That is, the ophthalmologic photographing apparatus according to the present embodiment may include a configuration that can match the amount of measurement light irradiated to the eye to be examined in any state in which the first profile is changed. Thereby, the light quantity in the return light of the measurement light irradiated to the eye to be examined can be easily compared between a plurality of different first profiles.

  For example, the ophthalmologic photographing apparatus according to the present embodiment includes an illumination optical system that emits irradiation light toward the subject eye and illuminates the subject eye, and a light receiving optical system that receives reflected light from the subject eye. An observation optical system that acquires a front image of the eye to be examined based on a light reception signal from the light reception optical system, and may be configured to include an observation optical system different from the OCT optical system. That is, the ophthalmologic photographing apparatus may be configured to include a configuration of an SLO (Scanning Laser Ophthalmoscope) or a fundus camera. Of course, an SLO or a fundus camera may be provided separately from the ophthalmologic photographing apparatus in the present embodiment. For example, in this case, an ophthalmic imaging apparatus may be connected to an SLO or a fundus camera, and the ophthalmic imaging apparatus may receive a front image of the eye to be examined acquired by the SLO or the fundus camera. In these ophthalmologic photographing apparatuses, the second changing means (for example, the control unit 70) changes the profile of the irradiation light in the illumination optical system, and changes the profile of the irradiation light to the same profile as the second profile. As a result, the examiner efficiently refers to the profile of the measurement light acquired in the apparatus equipped with the OCT optical system, and efficiently uses the second profile of the irradiation light in the apparatus equipped with the observation optical system different from the OCT optical system. Can be the same as the profile. In addition, in an apparatus provided with an observation optical system different from the OCT optical system, the eye to be examined can be photographed with high accuracy.

<Example>
Hereinafter, embodiments of the present disclosure will be described with reference to the drawings. FIG. 1 is an external configuration diagram of an ophthalmologic photographing apparatus 1 according to the present embodiment. For example, the ophthalmologic photographing apparatus 1 includes a base 101, a moving base 102, a measurement unit 103, an operation member 104, a face support unit 105, a drive unit 106, and a monitor 75. For example, the movable table 102 is movable in the left-right direction (X direction) and the front-back direction (Z direction) with respect to the base 101. For example, the measurement unit 103 houses an optical system described later. For example, the face support unit 105 is fixed to the base 101 in order to support the subject's face. For example, the drive unit 106 can move in the vertical direction (Y direction) with respect to the moving table 102. For example, the monitor 75 displays OCT data (for example, first OCT data and second OCT data) described later.

  For example, the operating member (joystick) 104 is provided with a moving mechanism that moves the measuring unit 103 relative to the eye E to be examined. More specifically, for example, the joystick 104 includes a sliding mechanism (not shown) that slides the moving base 102 in the XZ direction on the base 101. For example, when the joystick 104 is operated, the moving base 102 slides on the base 101 in the XZ direction. The joystick 104 is provided with a rotation knob. For example, when the joystick 104 is rotated, the drive unit 106 is driven in the Y direction, and the measurement unit 103 is moved in the Y direction. For example, the measurement unit 103 can be moved with respect to the eye E by this.

  In the present embodiment, the configuration in which the measurement unit 103 is moved in the Y direction by the drive unit 106 has been described as an example, but the present invention is not limited to this. For example, the measuring unit 103 may be provided with a moving mechanism that allows the measuring unit 103 to move in the XYZ directions. In this case, for example, a moving mechanism in the X, Y, and Z directions of the measuring unit 103 with respect to the eye E is used when the measuring unit 103 is finely moved, and a sliding mechanism of the moving table 102 coarsely moves the measuring unit 103. It may be used when making it.

  For example, the ophthalmologic imaging apparatus 1 in the present embodiment is an optical tomographic interferometer (hereinafter referred to as OCT device 1) that acquires depth information of the eye E to be examined. For example, the OCT device 1 may be Fourier domain optical coherence tomography (FD-OCT: Fourier Domain OCT) or time domain OCT (TD-OCT: Time Domain OCT). Typical examples of FD-OCT include spectral domain OCT (SD-OCT) and swept source OCT (SS-OCT). Of course, the present disclosure is applied to these apparatuses. Can be done.

  2A and 2B are schematic configuration diagrams illustrating an optical system and a control system of the ophthalmologic photographing apparatus 1 according to the present embodiment. FIG. 2A shows an optical arrangement at the time of fundus photography, and FIG. 2B shows an optical arrangement at the time of anterior eye photography. The OCT device 1 shown in FIGS. 2A and 2B mainly includes an interference optical system (OCT optical system) 2, a measurement optical system (light guide optical system) 20, and a control unit 70. The OCT device 1 in the present embodiment further includes a fixation target projection unit 90 (second optical system), a storage unit (memory) 72, an operation unit 74, and a monitor 75. For example, the OCT optical system 2, the measurement optical system 20, and the fixation target projection unit 90 are accommodated in the measurement unit 103 described above. In addition, for example, the control unit 70 and the storage unit 72 are accommodated in the moving table 102 described above.

  First, the OCT optical system 2 will be described. The OCT optical system 2 divides the light beam emitted from the light source 11 into measurement light and reference light. The OCT optical system 2 guides the measurement light to the eye E and guides the reference light to the reference optical system 30. Then, the OCT optical system 2 detects interference between the measurement light irradiated to the eye E and the reference light by the detector (light detector) 40. More specifically, in the present embodiment, the measurement light reflected (or backscattered) by the eye E and the interference light generated by combining the reference light are detected by the detector 40, and the interference signal is acquired.

  For example, in the case of SD-OCT, a low-coherent light source (broadband light source) is used as the light source 11, and the detector 40 is provided with a spectroscopic optical system (spectrum meter) that separates interference light into frequency components. For example, the spectrum meter is composed of a diffraction grating and a line sensor.

  For example, in the case of SS-OCT, a wavelength scanning light source (wavelength variable light source) that changes the emission wavelength at a high speed in time is used as the light source 11, and the detector 40 includes, for example, a single light receiving element. Provided. The light source 11 includes, for example, a light source, a fiber ring resonator, and a wavelength selection filter. Examples of the wavelength selection filter include a combination of a diffraction grating and a polygon mirror, and a filter using a Fabry-Perot etalon.

  In the OCT device 1, the optical arrangement of the measurement optical system 20 is switched. As an example, the optical arrangement shown in FIG. 2A may be switched to the optical arrangement shown in FIG. 2B. In the optical arrangements of FIGS. 2A and 2B, the depth zones of the portions where the tomographic image is captured by the OCT device 1 are different from each other. Hereinafter, in this embodiment, a case where SD-OCT is applied to the OCT device 1 will be described as an example.

  The OCT optical system 2 illustrated in FIGS. 2A and 2B includes a light source 11, optical fibers 15a, 15b, 15c, and 15d, a splitter 15, a reference optical system 30, and a detector 40.

  The light source 11 emits low coherent light used as measurement light and reference light of the OCT optical system 2. As the light source 11, for example, an SLD light source or the like may be used. More specifically, for example, the light source 11 may emit light having a center wavelength between λ = 800 nm and 1100 nm. Light from the light source 11 is guided to the splitter 15 through the optical fiber 15a.

  The optical fibers 15a, 15b, 15c, and 15d connect the splitter 15, the light source 11, the measurement optical system 20, the reference optical system 30, the detector 40, and the like by allowing light to pass therethrough.

  The splitter 15 splits the light guided from the light source 11 (through the optical fiber 15a) into measurement light and reference light. The measurement light is guided to the measurement optical system 20 through the optical fiber 15b. On the other hand, the reference light is guided to the reference optical system 30 via the optical fiber 15 c and the polarizer 31.

  2A and 2B, the divider 15 also serves as a coupling unit (combiner) that couples the return path of the measurement light guided to the eye E and the reference light (details will be described later). To do). Such a splitter 15 may be, for example, a fiber coupler. Hereinafter, the divider 15 is referred to as a coupler 15.

  For convenience, the measurement optical system 20 will be described here. For example, the measurement optical system 20 guides measurement light to the eye E to be examined. As an example, the measurement optical system 20 shown in FIGS. 2A and 2B includes a collimator lens 21, a changing member 28, a mirror 29, a light beam diameter adjusting unit 22, a condensing position variable optical system (condensing position variable lens system) 23, and scanning. Unit (optical scanner) 24, mirror 25, dichroic mirror 26, and objective optical system 27.

  The collimator lens 21 collimates the measurement light emitted from the end 16b of the optical fiber 15b.

  The change member 28 changes the profile of the measurement light applied to the eye E by locally changing the reflected light of the measurement light incident on the change member 28. For example, as the changing member 28, a DMD, an LCD (for example, a reflective LCD or a transmissive LCD), a wavefront modulation element, or the like can be used. In this embodiment, the case where DMD is used as the changing member 28 will be described as an example. For this reason, the changing member 28 is indicated as DMD 28 in the following.

  For example, in the DMD 28, a large number of minute mirrors P (see FIG. 6A) that can change the reflection angle are two-dimensionally arranged. For example, the DMD 28 can locally change the reflection direction of the measurement light incident on the DMD 28 by controlling the reflection angle of each minute mirror P. For this reason, the profile of the measurement light irradiated to the eye E is changed through the DMD 28. That is, the profile of the measurement light reflected by the DMD 28 has a shape different from the profile of the measurement light incident on the DMD 28 and is irradiated to the eye E.

  The DMD 28 may change the profile of the measurement light by switching each minute mirror P to two types of states. In this case, the DMD 28 changes the reflection angle of the minute mirror P to ON (for example, +12 degrees) or OFF (for example, −12 degrees). For example, the DMD 28 may reflect the measurement light in the direction of the mirror 29 and guide it to the eye E to be examined by turning on the minute mirror P. Further, for example, the DMD 28 may be configured such that the measurement light is reflected in the direction of the absorbing member (not shown) and not guided to the eye E by turning the minute mirror P in the OFF state.

  For example, the DMD 28 is disposed between the collimator lens 21 and the mirror 29. Note that the DMD 28 may be configured to be disposed at any position between the collimator lens 21 and the scanning unit 24, and is not limited to the present embodiment.

  The light beam diameter adjusting unit 22 is disposed in the optical path between the OCT optical system 2 and the scanning unit 24 (that is, the optical scanner), and is used for changing the light beam diameter of the measurement light in the optical path. 2A and 2B, the light beam diameter adjusting unit 22 is provided in the optical path between the coupler 15 and the scanning unit 24 in the measurement optical system 20. The light beam diameter adjusting unit 22 may be, for example, at least one of an aperture that can be inserted and removed from the optical path by an insertion and removal mechanism, a variable beam expander, and a variable aperture that can adjust the diameter of the aperture. For example, in this embodiment, the beam diameter adjusting unit 22 shown in FIGS. 2A and 2B is a variable beam expander. As shown in FIGS. 2A and 2B, the variable beam expander may include, for example, two lenses 22a and 22b and a drive unit 22c. The drive unit 22 c changes the positional relationship in the optical axis direction between the lenses 22 a and 22 b based on a control signal from the control unit 70. Thereby, the beam diameter (and numerical aperture NA) of the measurement light is changed.

  The condensing position variable optical system 23 is used to change the condensing position of the measurement light in the direction of the optical axis L1. The condensing position variable optical system 23 has at least one lens 23a, and adjusts the condensing position of the measurement light with respect to the direction of the optical axis L1 using the lens 23a. 2A and 2B, the condensing position variable optical system 23 is provided in the optical path between the coupler 15 and the scanning unit 24. In this embodiment, the condensing position variable optical system 23 is disposed between the light beam diameter adjusting unit 22 and the scanning unit 24. However, the arrangement of the light beam diameter adjusting unit 22 and the condensing position variable optical system 23 is not necessarily limited to this. For example, they may be replaced with each other. Further, a relay optical system or the like may be interposed between the two. The lens 23a constitutes a focus optical system that determines the collection position of the measurement light with respect to the optical axis L1 direction. The condensing position variable optical system 23 may be configured by the lens 23a alone, or may be configured together with the lens 23a and other optical elements. The condensing position variable optical system 23 is realized, for example, with a configuration that adjusts either the refractive power of the lens 23a or the positional relationship between the objective optical system 27 and the lens 23a in the optical axis L1 direction. The positional relationship between the objective optical system 27 and the lens 23a is adjusted by, for example, the position of the lens 23a in the direction of the optical axis L1, the optical path length between the lens 23a and the objective optical system 27a, and the lens relative to the measurement optical path. It may be realized by either insertion or removal. In this case, the drive unit (actuator) that moves the lens 23 a in the intended direction is controlled by the control unit 70.

  In the example of FIGS. 2A and 2B, the lens 23a is a variable focus lens. The lens 23a can change the focal position while being stationary with respect to the optical axis L1. The lens 23 a changes the refractive power according to the magnitude of the applied voltage set by the control unit 70. A liquid crystal lens or the like is known as a typical variable focus lens. The lens with variable refractive power is not limited to a liquid crystal lens, and may be, for example, a liquid lens, a nonlinear optical member, a molecular member, a rotationally asymmetric optical member, or the like.

  The scanning unit 24 includes an optical scanner that deflects the measurement light from the OCT optical system in order to scan the measurement light. For example, the scanning unit 24 may include two galvanometer mirrors 241 and 242 (an example of an optical scanner). In the example of FIG. 3, reference numeral 241 denotes an X scanning galvanometer mirror, and 242 denotes a Y scanning galvanometer mirror. Each of the galvanometer mirrors 241 and 242 may include mirror units 241a and 242a and driving units 241b and 242b (for example, motors) that rotate the respective 241a and 242a. The control unit 70 changes the traveling direction of the measurement light by independently controlling the directions of the galvanometer mirrors 241 and 242. As a result, the measurement light can be scanned in the vertical and horizontal directions with respect to the eye E. The scanning unit 24 can use an optical scanner other than the galvanometer mirrors 241b and 242b. For example, a reflective scanner (for example, a MEMS scanner, a resonant scanner, a polygon mirror, or the like) may be used, or an acousto-optic element may be used.

  In the example of FIGS. 2A and 2B, the measurement light whose traveling direction has been changed by the scanning unit 24 is reflected by each of the mirror 25 and the dichroic mirror 26 in which the mirror surfaces are arranged with a right angle therebetween. As a result, the measurement light is folded back in the direction opposite to that emitted from the scanning unit 24. As a result, the measurement light is guided to the objective optical system 27.

  In the present embodiment, the objective optical system 27 is fixedly arranged. More specifically, the objective optical system 27 is arranged between the scanning unit 24 and the eye E in the measurement optical system 20. The objective optical system 27 guides the measurement light deflected by the optical scanner (galvano mirrors 241 and 242 in this embodiment) to the eye E to be examined. In this embodiment, the objective optical system 27 is formed as a lens system (objective lens system) having a positive power. For this reason, the measurement light from the scanning unit 24 is bent toward the optical axis L <b> 1 by passing through the objective optical system 27. 2A and 2B, for convenience, the objective optical system 27 is shown as an optical system including two lenses 27a and 27b. However, the number of lenses constituting the objective optical system 27 is not limited to this. . The objective optical system 27 may be replaced with one lens, or may be replaced with three or more lenses. The objective optical system 27 is not limited to a lens system. For example, the objective optical system 27 may be a mirror system, an optical system based on a combination of a lens and a mirror, or an optical system other than a lens and a mirror. An optical system including a member may be used.

  In such a measurement optical system 20, when the measurement light is emitted from the end portion 16 b of the optical fiber 15 b, the measurement light is collimated by the collimator lens 21. Further, the profile of the measurement light is changed by the DMD 28. Thereafter, the measurement light is reflected by the mirror 29, passes through the light beam diameter adjusting unit 22 and the condensing position variable optical system 23, and reaches the scanning unit 24. The measurement light is reflected by two galvanometer mirrors provided in the scanning unit 24 and then further reflected by the mirror 25 and the dichroic mirror 26. As a result, the measurement light enters the objective optical system 27. Then, the measurement light passes through the objective optical system 27 and is guided to the eye E to be examined. Thereafter, the measurement light is reflected or scattered by the eye E, and as a result, the measurement light system 20 travels backward to enter the end portion 16b of the optical fiber 15b. The measurement light incident on the end portion 16b enters the coupler 15 through the optical fiber 15b.

  The OCT device 1 includes a drive unit (actuator). The drive unit displaces the relative position of the scanning unit 24 (that is, the galvanometer mirrors 241 and 242 which are optical scanners) with respect to the objective optical system 27 and the relative position of the measurement optical system 20 in the optical axis L1 direction. More specifically, the relative position of the scanning unit 24 with respect to the rear focal position (or its conjugate position) of the objective optical system 27 is changed by driving the driving unit. Due to the displacement of the relative position, the turning position of the measurement light is changed with respect to the direction of the optical axis L1. The drive unit displaces the relative distance of the scanning unit 24 with respect to the objective optical system 27 by moving at least one of the scanning unit 24 and the optical member disposed between the objective optical system 27 and the scanning unit 24. You may let them. 2A and 2B, the OCT device 1 has a drive unit 50. The distance (optical path length) between the objective optical system 27 and the scanning unit 24 is changed by driving the driving unit 50, and thereby the relative position of the scanning unit 24 with respect to the objective optical system 27 is displaced. This relative position is changed in correspondence with the depth zone of the eye E to be imaged.

  In the example of FIGS. 2A and 2B, the driving unit 50 integrally moves two mirrors (mirror 25 and dichroic mirror 26) each having a mirror surface sandwiching a right angle in a predetermined direction. In the present embodiment, the objective optical system 27 is moved in the optical axis direction. As a result, the optical path length from the scanning unit 24 to the objective optical system 27 is changed (for example, FIG. 2A → FIG. 2B, FIG. 2B → FIG. 2A). For example, when the depth zone where a tomographic image is obtained is switched between the anterior segment Ec and the fundus oculi Er, it is necessary to change the optical path length from the scanning unit 24 to the objective optical system 27 relatively large. On the other hand, in the example of FIG. 2A, the measurement light emitted from the scanning unit 24 is folded back by two mirrors, so that when the two mirrors are moved, from the scanning unit 24 to the objective optical system 27. (In other words, the amount of displacement of the scanning unit 24 in the direction of the optical axis L1 with respect to the objective optical system 27) can be twice the amount of movement of the two mirrors 25 and 26. Therefore, a space necessary for displacing the position of the scanning unit 24 with respect to the objective optical system 27 with respect to the optical axis L1 direction of the measurement optical system 20 can be suppressed.

  2A and 2B, the OCT device 1 may include a sensor 51 for detecting the position of the scanning unit 24 with respect to the objective optical system 27. Various devices can be used as the sensor 51. For example, a linear displacement sensor such as a potentiometer may be applied as the sensor 51.

  Here, the description returns to the OCT optical system 2. The reference optical system 30 generates reference light. The reference light is light that is combined with the reflected light of the measurement light reflected by the fundus Er. The reference optical system 30 may be a Michelson type or a Mach-Zehnder type. The reference optical system 30 illustrated in FIGS. 2A and 2B is formed by a reflection optical system (for example, a reference mirror 34). In the example of FIGS. 2A and 2B, the light from the coupler 15 is reflected back by the reflection optical system, and is returned to the coupler 15 again. As a result, the light is guided to the detector 40. The reference optical system 30 is not necessarily limited to this, and may be formed by a transmission optical system (for example, an optical fiber). In this case, the reference optical system 30 guides the reference light divided by the coupler 15 to the detector 40 by transmitting the reference light without returning to the coupler 15.

  2A and 2B, the reference optical system 30 has an optical fiber 15c, an end portion 16c of the optical fiber 15c, a collimator lens 33, and a reference mirror 34 in the optical path from the splitter 15 to the reference mirror 34. doing. The optical fiber 15c is rotated by the drive unit 32 in order to change the polarization direction of the reference light. That is, the optical fiber 15c and the drive unit 32 are used as a polarizer 31 for adjusting the polarization direction. The polarizer is not limited to the above-described configuration, and any polarizer may be used as long as the polarization state of the measurement light and the reference light is substantially matched by driving the polarizer arranged in the optical path of the measurement light or the optical path of the reference light. . For example, a half-wave plate or a quarter-wave plate can be used, or one that changes the polarization state by applying pressure to the optical fiber to deform it can be applied.

  The polarizer 31 (polarization controller) may be configured to adjust the polarization direction of at least one of the measurement light and the reference light in order to match the polarization directions of the measurement light and the reference light. For example, the polarizer 31 may be configured in the optical path of the measurement light.

  The reference mirror 34 is displaced with respect to the optical axis direction L2 by the reference mirror driving unit 34a. As the reference mirror 34 is displaced, the optical path length of the reference light is adjusted.

  The reference light emitted from the end 16 c of the optical fiber 15 c is converted into a parallel light beam by the collimator lens 33 and reflected by the reference mirror 34. Thereafter, the reference light is collected by the collimator lens 33 and enters the end 16c of the optical fiber 15c. The reference light incident on the end 16c reaches the coupler 15 via the optical fiber 15c and the optical fiber 31 (polarizer 31).

  In the example of FIGS. 2A and 2B, the reference light reflected by the reference mirror 34 and the return light of the measurement light guided to the eye E (that is, the measurement light reflected or scattered by the eye E) Are combined by the coupler 15 to be interference light. This interference light is emitted from the end portion 16d through the optical fiber 15d. As a result, the interference light is guided to the detector 40.

  In order to obtain an interference signal for each frequency (wavelength), the detector (here, the spectrometer unit) 40 separates the interference light by the reference light and the measurement light for each frequency (wavelength), and the split interference light is obtained. Receive light.

  The detector 40 shown in FIGS. 2A and 2B may include, for example, an optical system (not shown) such as a collimator lens, a grating mirror (diffraction grating), and a condenser lens. For example, a one-dimensional light receiving element (line sensor) may be applied to the main body (light receiving element portion) of the detector 40. The detector 40 is sensitive to the wavelength of light emitted from the light source 11. As described above, when infrared light is emitted from the light source 11, the detector 40 having infrared sensitivity can be used.

  The interference light emitted from the end portion 16b is converted into parallel light by the collimator lens 21, and then split into frequency components by a grating mirror (not shown). Then, the interference light split into frequency components is condensed on the light receiving surface of the detector 40 via a condenser lens (not shown). Thereby, spectrum information (spectrum signal) of interference fringes on the detector 40 is obtained. The spectrum information is input to the control unit 70 and analyzed by the control unit 70 using Fourier transform. As a result of the analysis, a tomographic image of the eye E is formed. In addition, as an analysis result, information in the depth direction of the eye E can be measured.

  Here, the control unit 70 can acquire a tomographic image by scanning the measurement light in the transverse direction of the eye E with the scanning unit 24. For example, by scanning in the X direction or the Y direction, a tomographic image on the XZ plane or the YZ plane of the fundus Er to be examined can be acquired (in this embodiment, the measurement light is primarily applied to the fundus Er in this way. A method of performing original scanning and obtaining a tomographic image is referred to as B-scan). Note that the acquired tomogram is stored in the storage unit 72 connected to the control unit 70. Further, by controlling the driving of the scanning unit 24 and scanning the measurement light in the XY direction two-dimensionally, a two-dimensional moving image of the eye fundus Er in the XY direction and a three-dimensional image of the eye fundus Er in the eye to be inspected. Can be formed based on the output signal from the detector 40.

  Next, the fixation target projection unit 90 will be described. The fixation target projecting unit 90 has an optical system for guiding the line-of-sight direction of the eye E. The fixation target projection unit 90 includes a fixation target (fixation light source 91) to be presented to the eye E. The fixation target projection unit 90 may be configured to guide the eye E in a plurality of directions. Here, the dichroic mirror 26 has a characteristic of reflecting light of a wavelength component used as measurement light of the OCT optical system 2 and transmitting light of a wavelength component used for the fixation target projection unit 90. Therefore, the fixation target luminous flux emitted from the fixation target projection unit 90 is irradiated to the eye E through the objective optical system 27. As a result, the subject can fixate.

<Control system>
Next, the control system of the OCT device 1 will be described. The control unit (controller) 70 controls each unit of the OCT device 1. For example, the control unit 70 may include a CPU (processor) and a memory. In the present embodiment, the control unit 70 acquires the depth information of the eye E by processing an output signal (that is, an interference signal) from the detector 40, for example. Depth information includes image information such as tomograms, dimensional information indicating the dimensions of each part of the eye E, information indicating the amount of movement in the irradiated region of the measurement light, and a (complex number) analysis signal including information on polarization characteristics, And / or the like. In the present embodiment, the control unit 70 also serves as an image processor that forms a tomographic image of the eye E based on the interference signal. Further, the control unit 70 according to the present embodiment performs various image processing in addition to the formation of the tomographic image. The image processing may be performed by a dedicated electronic circuit (for example, an image processing IC not shown) provided in the control unit 70, or may be performed by a processor (for example, CPU).

  A storage unit 72, an operation unit (user interface) 74, and a monitor 75 are connected to the control unit 70 (see FIGS. 2A and 2B). The storage unit 72 may include a rewritable non-transitory storage medium, and may be any one of a flash memory and a hard disk, for example. Images and measurement data obtained as a result of photographing and measurement are stored in the storage unit 72. The program and fixed data defining the imaging sequence in the OCT device 1 may be stored in the storage unit 72 or may be stored in the ROM in the control unit 70. In addition to the light source 11, the detector 40, and various driving units 22c, 23a, 241a, 242b, 32, 34a, 50, a sensor 51 and the like are connected.

<Shooting depth zone switching operation>
For example, the OCT device 1 having the above configuration may switch the depth zone of the imaging region in the eye E. In this case, the control unit 70 controls the driving unit 50 to switch the turning position of the measurement light in the eye E with respect to the direction of the optical axis L1. The turning position is displaced according to the relative position of the scanning unit 24 with respect to the objective optical system 27. That is, in this embodiment, the control unit 70 changes the relative position of the scanning unit 24 with respect to the objective optical system 27 by the driving unit 50, and as a result, the swiveling position of the measurement light in the eye E with respect to the optical axis L1 direction. adjust. At that time, the control unit 70 changes the turning position of the measurement light at least between the first position and the second position. The first position corresponds to a first depth zone of the eye E (for example, the anterior segment Ec of the eye E), and the second position is a second depth zone of the eye E that is different from the first depth zone ( For example, it corresponds to the fundus oculi Er) of the eye E to be examined. The second position is different from the first position with respect to the optical axis direction of the measurement optical system (the depth direction of the eye E).

  In addition, when the swiveling position of the measurement light in the eye E is switched with respect to the direction of the optical axis L1, the control unit 70 is linked with the change of the relative position between the objective optical system 27 and the scanning unit 24, and the reference optical system 30. The optical path length at may be adjusted. Further, the control unit 70 may control the condensing position variable optical system 23 to switch the condensing position of the measurement light. Further, the control unit 70 may control the light beam diameter adjusting unit 22 to adjust the NA. Such a change in the position of the scanning unit 24 (in other words, a change in the imaging depth band) may be executed based on, for example, a switching signal output from the operation unit 74 to the control unit 70. Further, the control unit 70 may automatically switch in a series of shooting sequences.

  For example, at the time of anterior segment imaging of the eye E, as shown in FIG. 2B, the control unit 70 brings the scanning unit 24 closer to the objective optical system 27 at the time of fundus imaging (see FIG. 2A). At this time, on the object side (the eye side to be examined) of the objective optical system 27, the principal ray of the measurement light is telecentric (or substantially telecentric). That is, in this embodiment, the optical system including the scanning unit 24 and the objective optical system 27 is formed as an object side telecentric optical system. In this case, the turning position of the measurement light in the eye E (the first position in the present embodiment) can be considered as an infinite point on the optical axis L1. In this case, the principal ray of the measurement light emitted from the front surface of the objective optical system 27 (that is, the lens surface arranged closest to the eye to be examined) to the pupil surface of the eye E is reflected by the scanning unit 24. Regardless of the direction of the measurement light, it is parallel (substantially parallel) to the optical axis L1.

  On the other hand, at the time of fundus photographing, as shown in FIG. 2A, the control unit 70 moves the scanning unit 24 away from the objective optical system 27 as compared to the time of photographing the anterior eye part (see FIG. 2B). At this time, the measurement light emitted from the front surface (lens surface closest to the eye to be examined) of the objective optical system 27 as the scanning unit 24 is driven rotates around the pupil position (swivel point). That is, in this case, the turning position of the measurement light in the eye E (second position in the present embodiment) is set as the pupil position.

  For the positional relationship and details of the measurement optical system 20 at the time of anterior segment imaging of the eye E and at the fundus imaging, refer to JP-A-2006-209577.

<Control action>
Hereinafter, the control operation of the OCT device 1 having the above configuration will be described in order with reference to the flowchart shown in FIG. For example, the ophthalmologic imaging apparatus 1 includes an anterior ocular segment imaging mode for imaging the anterior ocular segment Ec of the eye E to be examined and a fundus imaging mode for imaging the fundus oculi Er of the eye E to be examined. An example of applying the shooting mode will be described. For example, in the fundus imaging mode, the measurement light is irradiated onto the fundus through the pupil plane of the eye to be examined. In this case, measurement light having a certain diameter may be irradiated to the pupil surface of the eye E to be examined.

  For example, the examiner instructs the subject to watch the fixation target of the fixation target projection unit 90. An alignment index image Ma to Mh described later is projected onto the eye E by turning on a light source of an index projection optical system (not shown). Further, the anterior segment Ec of the eye E is detected by an anterior segment imaging optical system (not shown), and the anterior segment observation image 60 (see FIG. 5) is displayed on the monitor 75.

<Alignment of eye to be examined (S1)>
For example, the control unit 70 detects the alignment state between the eye E and the measurement optical system 20 using the alignment index images Ma to Mh. In addition, the control unit 70 controls the moving table 102 and the driving unit 106 to move the measurement unit 103, whereby the corneal apex position (or substantially the corneal apex position) of the eye E to be examined and the optical axis L1 of the measurement light. Are automatically aligned (S1).

  FIG. 5 is a view showing an anterior ocular segment observation image 60 of the eye E to be examined. For example, the alignment state of the eye E in the left-right direction (X direction) and the up-down direction (Y direction) is determined using an alignment reference position set in advance at a position where the corneal apex position matches the optical axis L1. . For example, the control unit 70 detects the ring-shaped XY center coordinates (cross marks shown in FIG. 5) in the index images Ma to Mh as the corneal apex position. Further, the control unit 70 obtains a deviation amount in which the detected corneal vertex position of the eye E to be detected is shifted in the XY direction with respect to the alignment reference position. For example, the control unit 70 moves the measurement unit 103 so that the deviation amount becomes 0, and adjusts the alignment in the X direction and the Y direction with respect to the eye E. An allowable range for determining the suitability of alignment may be set in a predetermined region in the XY direction centered on the alignment reference position, and the measurement unit 103 may be moved so as to be within this allowable range. .

  For example, the alignment state of the eye E in the front-rear direction (Z direction) is determined using the alignment index images Ma to Mh. For example, the index images Ma and Me are at infinity, and the index images Mh and Mf are at finite distance. For example, in the present embodiment, when the eye E is in an appropriate position with respect to the OCT device 1 (that is, when there is no displacement in the Z direction), the image interval a from the index image Ma to Me at infinity And the image interval b from the finite index image Mh to Mf is set to have a certain ratio. For example, when the eye E to be examined is not in an appropriate position with respect to the OCT device 1 (that is, when there is a displacement in the Z direction), the image interval a hardly changes, but the image interval b changes. For example, the control unit 70 compares the image ratio (that is, a / b) between the image interval a and the image interval b, and adjusts the alignment in the Z direction so that this becomes a constant ratio (for details, refer to Japanese Laid-Open Patent Application No. 6-6 No. 46999). Of course, an allowable range for determining the suitability of alignment may be set in a predetermined region in the Z direction centered on the alignment reference position, and the measurement unit 103 may be moved so as to be within this allowable range. .

<Implementation of optimization control (S2)>
Next, the control unit 70 starts optimizing shooting conditions (S2). For example, by performing optimization control, the fundus site desired by the examiner can be observed with high sensitivity and high resolution. For example, the optimization control includes optical path length adjustment, focus adjustment, and polarization state adjustment (polarizer adjustment).

  For example, in this embodiment, optimization control is performed in the order of the first automatic optical path length adjustment, the focus adjustment, the second automatic optical path length adjustment, and the polarizer adjustment. For example, the control unit 70 sets the position of the reference mirror 34 to the initial position, and sets the refractive power of the lens 23a to 0D. When the initialization is completed, the control unit 70 moves the reference mirror 34 in one direction from the initial position in a predetermined step, and performs the first optical path length adjustment (first automatic optical path length adjustment). When the first optical path length adjustment is completed, the control unit 70 performs autofocus adjustment (focus adjustment) by changing the refractive power of the lens 23a so as to focus on the anterior segment of the eye E. When the autofocus adjustment is completed, the control unit 70 moves the reference mirror 34 in the direction of the optical axis L2 to adjust the second optical path length (second automatic optical path length adjustment) for readjustment of the optical path length (fine adjustment of the optical path length). )I do. When the second optical path length adjustment is completed, the control unit 70 adjusts the polarization state of the measurement light by moving the polarizer 31 to a position where the interference light can be strongly received (that is, a position where the polarization state of the measurement light and the reference light matches). To do.

<Change to first profile of measurement light (S3)>
For example, the control unit 70 changes the profile of the measurement light in the OCT optical system 2 by controlling the DMD 28. For example, in this embodiment, a case where the profile of the measurement light is changed by switching the state of the minute mirror P in the DMD 28 (that is, the ON state and the OFF state) will be described as an example. As a result, the profile of the measurement light is changed to the first profile 100 (S3). Note that the measurement light profile may be changed to at least two different first profiles. In addition, as the first profile 100, among the measurement light emitted toward the fundus of the eye to be examined, any part of the eye to be examined in the path from the anterior segment to the fundus (for example, the pupil plane of the eye to be examined (pupil surface) ), The distribution of measurement light in the vitreous body and the like may be changed.

  FIG. 6 is a diagram for explaining the DMD 28. For example, in this embodiment, each of the gratings in FIG. 6 is represented as a minute mirror P (P1 to P16) included in the DMD 28. Further, for example, the shape indicated by the dotted line in FIG. 6 represents the outer diameter 80 of the measurement light before entering the DMD 28. That is, in the present embodiment, 16 micro mirrors P are arranged at the position where the measurement light is incident on the DMD 28.

  FIG. 7 is a diagram showing the relationship between the DMD 28 and the first profile 100. FIG. 7A shows a state in which the reflection angle of the minute mirror P is switched. In FIG. 7A, a minute mirror P in which the reflection angle is ON is indicated by a white area, and a minute mirror P in which the reflection angle is OFF is indicated by a hatched area. FIG. 7B shows the first profile 100 (first profiles 100a to 100d) of the measurement light emitted to the eye E corresponding to the DMD 28 in the state of FIG. 7A.

  For example, when all the minute mirrors P are in the ON state (B1 in FIG. 7A), the profile of the measurement light incident on the DMD 28 is changed to the first profile 100a. That is, the measurement light is reflected in the direction of the mirror 29 by all the minute mirrors P1 to P16 and guided to the eye E to be examined. At this time, an irradiation region 110 in which the measurement light is irradiated to the eye E is created in the first profile 100a. For example, when all the minute mirrors P are in the OFF state (B4 in FIG. 7A), the profile of the measurement light incident on the DMD 28 is changed to the first profile 100d. That is, the measurement light is reflected in the direction of the absorbing member (not shown) by all the minute mirrors P1 to P16 and is not guided to the eye E to be examined. At this time, a non-irradiation region 120 where the measurement light is not irradiated onto the eye E is created in the first profile 100d.

  For example, when some of the minute mirrors P are ON and the other minute mirrors P are OFF (B2 or B3 in FIG. 7A), the profile of the measurement light incident on the DMD 28 is The first profile 100b or the first profile 100c is changed. At this time, only the measurement light incident on the minute mirror P shown in the white area (in other words, the minute mirror P whose reflection angle is in the ON state) is guided to the eye E. The measurement light incident on the minute mirror P (in other words, the minute mirror P in which the reflection angle is OFF) indicated by the hatched area is not guided to the eye E. That is, the irradiation region 110 and the non-irradiation region 120 are created in the first profile 100b and the first profile 100c.

  For example, the measurement light after being incident on the DMD 28 in this manner can be changed to the first profile 100 to change various pattern shapes (for example, a regular pattern shape, an irregular pattern shape, a random pattern shape, etc.) ). For example, the control unit 70 in the present embodiment can change the profile of the measurement light to various different first profiles 100 by controlling the DMD 28 and changing the profile of the measurement light in various ways.

  For example, in the present embodiment, in the state where the profile of the measurement light is changed to a plurality of different first profiles 100, the amount of measurement light irradiated to the eye E is set to be the same. For example, in this case, the control unit 70 may be configured such that the total amount of light in the measurement light applied to the eye to be examined is equal. For example, as a configuration in which the amount of measurement light is set to be the same, by changing the area of the irradiation region 110 in the first profile 100 according to the intensity of the measurement light from the light source 11, the measurement light irradiated to the eye E is measured. The amount of light may be the same. For example, as a configuration in which the light amount of the measurement light is set to be the same, the light amount of the measurement light applied to the eye E may be made the same by changing the output of the light source 11. Of course, by changing the area of the irradiation region 110 in the first profile 100 and the output of the light source 11, the amount of measurement light irradiated to the eye E may be made the same. In the present embodiment, the intensity of the measurement light from the light source 11 is uniform everywhere, and the area E of the irradiation region 110 in the first profile 100 is kept constant so that the eye E is irradiated. An example is given of the case where the amount of measurement light is set to be the same.

  For example, the control unit 70 controls the minute mirror P included in the DMD 28 so that the area of the irradiation region 110 is the same in any first profile. For example, in such a case, the memory 72 stores in advance only the first profile 100 in which the area of the irradiation region 110 is the same (that is, the number of minute mirrors P in which the reflection angle is ON is the same). Also good. In such a case, the memory 72 may store in advance a mixture of the first profile 100 having the same area of the irradiation region 110 and the first profile 100 having a different area of the irradiation region 110. For example, the control unit 70 selects the first profile 100 having the same area of the irradiation region 110 from the first profiles 100 stored in the memory 72, and switches the state of the minute mirror P corresponding thereto.

  For example, in the first profile 100b and the first profile 100c in FIG. 7B, eight of the 16 minute mirrors P are in the OFF state, and the area of the irradiation region 110 is the same. Of course, the number of minute mirrors P to be turned off is not limited to this embodiment. Thereby, when the light source 11 is irradiated to the eye E with a constant output, the light amount of the measurement light can be set to be the same. Note that the amount of measurement light emitted to the eye to be examined is not necessarily the same, and the first profiles 100 having different areas of the irradiation region 110 may be selected and set. In this case, the first OCT data may be acquired in the same manner as described below by appropriately standardizing a predetermined signal intensity obtained for each first profile.

<Acquisition of first OCT data (S4)>
For example, the control unit 70 irradiates the eye E with the measurement light in a state where the profile of the measurement light is changed to a plurality of different first profiles 100, and acquires first OCT data corresponding to each first profile. (S4). For example, the first OCT data may be the OCT signal itself from the detector 40, tomographic image data of the eye E, motion contrast data, or polarization characteristic data. It may be. For example, in the present embodiment, a tomographic image signal in the eye E is acquired as the first OCT data. In the present embodiment, for the sake of convenience, the first OCT data will be described by taking a wide-angle fundus image as an example, but the present invention is not limited to this. For example, the first OCT data may be a fundus image with a narrow angle. For example, in this case, it becomes easy to detect a predetermined position such as the fovea. Further, for example, the first OCT data may be an image (M scan image) obtained by continuously capturing the same position without performing any scanning. Of course, the first OCT data may be obtained by obtaining a predetermined number of times and taking the average.

  For example, the control unit 70 changes the profile of the measurement light to a plurality of first profiles 100 and acquires a plurality of first OCT data corresponding to each first profile 100. That is, in this embodiment, the profile of the measurement light is changed to a plurality of first profiles that are different from each other as a profile for provisional imaging. In the present embodiment, each first OCT data is acquired in the profile for provisional imaging.

<Analysis of first OCT data (S5)>
For example, the control unit 70 detects the predetermined signal strength in each first profile by analyzing the acquired first OCT data (S5). The OCT signal may be configured to analyze a signal before Fourier transform, or may be configured to analyze a signal after Fourier transform. For example, in this embodiment, the total amount of the OCT signal is detected as the signal intensity by analyzing the signal before Fourier transform. For example, in this case, the control unit 70 may obtain an envelope of the OCT signal and detect a value obtained by integrating the envelope as a total amount. The predetermined signal intensity may be obtained by integrating absolute values in a part of the wavelength region or part of the frequency region of the first OCT data, or may be a feature amount such as a peak, contrast, or histogram. Good. In addition, these wavelength regions or frequency regions may be regions set in advance by experiments or simulations, or may be arbitrarily settable. Thereby, for example, the control unit 70 obtains information on which path the measurement light has propagated using the relationship between the predetermined signal intensity detected for each first OCT data and the set first profile 100. be able to.

<Creation of transmittance distribution (S6)>
For example, the control unit 70 may create the transmittance distribution 85 using information on which path the measurement light has propagated (S6). For example, the transmittance distribution 85 is a distribution that can specify a position where the return light of the measurement light irradiated to the eye E is easily transmitted or a position where it is difficult to transmit at a position on the pupil of the eye E. is there. The transmittance distribution may be data indicating the amount of return light of the measurement light at each position on the pupil of the eye E, or data indicating the transmittance obtained from the amount of return light of the measurement light. It may be. Further, the transmittance distribution may be image data obtained by visualizing (for example, mapping) data such as the light amount and transmittance of the return light of the measurement light. In the present embodiment, an example is shown in which the transmittance of the return light of the measurement light is obtained as the transmittance distribution 85 and is shown as a map.

  FIG. 8 is a diagram for explaining the transmittance distribution 85. FIG. 8A shows the position of the eye E on the pupil. FIG. 8B shows a map of the transmittance distribution 85. For example, each of the lattices in FIG. 8A indicates the positions E1 to E16 on the pupil of the eye E to be examined. In the present embodiment, the positions of the positions E1 to E16 on the pupil of the eye E and the minute mirrors P1 to P16 of the DMD 28 correspond to each other. That is, the measurement light reflected by the minute mirror P1 of the DMD 28 passes through the position E1 on the pupil of the eye E and reaches the fundus Er. Further, the return light of the measurement light that has passed through the position E1 on the pupil of the eye E is reflected by the minute mirror P1 of the DMD 28 and reaches the coupler 15.

  Here, for example, the measurement light does not necessarily reach the fundus Er of the eye E to be examined. For example, if there is a eyelid of the eye E or turbidity generated in the eye E at a position where the measurement light is incident, the measurement light may be blocked by these. Further, for example, the return light of the measurement light does not necessarily reach the coupler 15 through the same position on the optical path through which the measurement light has passed. The return light of the measurement light may be scattered and reflected by the shape of the fundus oculi Er or the like, and may pass through different positions on the optical path through which the measurement light has passed. Further, the return light of the measurement light is reflected in the direction of the coupler 15 by being blocked by the eyelids of the eye E or the turbidity generated in the eye E or entering the minute mirror P in the OFF state. There may be no.

  This will be described in more detail. For example, when only the minute mirrors P1 and P3 of the DMD 28 are in the ON state, a part of the measurement light incident on the DMD 28 is reflected by the minute mirror P1 and travels toward the eye E. At this time, the return light of the measurement light scattered and reflected from the fundus Er is incident on the DMD 28, reflected by the minute mirror P1 and reaching the coupler 15, and reflected by the minute mirror P3 and the coupler. There are return light that reaches 15 and return light that does not reach the coupler 15 by being reflected by the minute mirror P (that is, the minute mirrors P2, P4 to P16) in the OFF state. Note that the return light of the measurement light reflected from the minute mirror P3 and directed to the eye E to be scattered and reflected from the fundus Er can be described in the same manner as described above, and is therefore omitted.

  For example, the minute mirrors P1 to P16 are set to have a specific first profile, and the measurement light incident on each of the positions E1 to E16 on the pupil of the eye E is scattered by the fundus Er of the eye to be examined, or After reflection, when the signal is detected again through the positions E1 to E16 on the pupil of the eye E and the minute mirrors P1 to P16, the predetermined signal intensity A is given by the following equation.

  Here, x of the bold body is a column vector display representing the ON or OFF state of the minute mirrors P1 to P16 as 1 or 0, respectively, and x with T on the right shoulder is transposed. Meaning a row vector. Accordingly, for example, when P3, P4, P7, and P9 to P16 are in the ON state among the minute mirrors P1 to P16 included in the DMD 28, the following expression can be used.

  This means that if the minute mirror P is in the ON state, the measurement light incident on the minute mirror P is reflected toward the mirror 29 without loss and guided to the eye E to be examined. On the contrary, if the minute mirror P is in the OFF state, the measurement light incident on the minute mirror P is reflected in the direction of the absorbing member (not shown) and is not guided to the eye E to be examined. This means that there is no contribution to (ie, the contribution is zero).

  The italic T is collected again through the positions E1 to E16 on the pupil of the eye E and the minute mirrors P1 to P16 when the measurement light enters the positions E1 to E16 on the pupil of the eye E. This represents how much each path contributes, and is called a transfer matrix. For example, the (4, 7) component of T is the measurement light incident from a position E7 on the pupil of the eye E corresponding to the minute mirror P7, and finally the pupil of the eye E corresponding to the minute mirror P4. This represents how much the path through which the return light of the measurement light is collected from the upper position E4 contributes to the predetermined signal intensity A.

  For example, the control unit 70 substitutes a predetermined signal intensity A of the first OCT data and the state x of the minute mirror P into the above-described Equation 1 to obtain 1 for each state of the DMD 28 that provides one first profile. A conditional expression regarding the components of two transfer matrices T is obtained. Therefore, by acquiring a plurality of different first profiles 100 one after another, each component of the transfer matrix can be obtained from a plurality of conditional expressions by simultaneous equations, so that the positions E1 to E16 on the pupil of the eye E to be examined can be obtained. It is possible to determine how much each path contributes until the measurement light is incident on each of them and is collected again through positions E1 to E16 on the pupil of the eye E and minute mirrors P1 to P16. In this case, the number of variations of the first profile 100 to be acquired is generally required by the number of variables, but the number may be reduced by making a certain assumption. For example, in this case, a method (sparse modeling) that assumes sparsity may be used. Note that sparse modeling is widely used in CT (Computed Tomography) reconstruction, and details thereof are described in Quant Imaging Med Surg 2013; 3 (3): 147-161 and the like, and thus are omitted. Further, for example, when a certain assumption is made, an assumption that there is no steep change may be made, and a path that is clearly easy to pass through the measurement light confirmed in the anterior eye observation image 60 is the transfer matrix T. It may be assumed that the component is larger than the others. Further, based on the OCT image of the anterior segment imaged in advance by the ophthalmologic imaging apparatus 1, it may be set in advance which component is how large. Of course, the variables may be reduced by handling specific positions such as E1 and E2 or E3 and E4 in a lump.

  For example, the control unit 70 may obtain the transmittance at a position on the pupil from the transfer matrix T. For example, various methods can be considered in this case, but the transmittance at the position on the pupil may be obtained by decomposing the transfer matrix T as shown in the following equation.

  In Equation 3, Max () is a function that selects the maximum value of the components of T and is used for normalization. The bold body t represents the transmittance of the measurement light incident on each of the positions E1 to E16 on the pupil of the eye E as a column vector. This is a Cartesian product operation that generates a matrix having values obtained by multiplying the components of each column. This is not necessarily determined uniquely, but may be obtained with the aid of a method for reducing the error (for example, a method such as a least square method).

  For example, when the third component of t is calculated as 0.5, the control unit 70 may determine that the transmittance at the position E3 on the pupil is 50%. For example, the control unit 70 may create a transmittance distribution 85 as shown in FIG. 8B by obtaining the transmittance at each position on the pupil and mapping it.

  Note that the transmittance at a position on the pupil is not limited to the present embodiment, and a known weight for each path may be set based on a design value or the like, and the transfer matrix T may be decomposed based on this. When attaching such weights, the transfer matrix T may be decomposed as in the following mathematical formula. Note that W is a matrix representing the weight for each route, but this is known if it is obtained from experiments, simulations, etc., and can be decomposed in the same manner as Equation 3.

<Change to Second Profile of Measurement Light (S7)>
For example, the control unit 70 changes the profile of the measurement light to a new second profile 200 different from the first profile 100 as the main imaging profile based on the plurality of acquired first OCT data (S7). For example, in this embodiment, the profile of the measurement light is changed to the second profile 200 based on the created transmittance distribution 85.

  FIG. 9 is a diagram for explaining the second profile 200. For example, the control unit 70 may turn off the minute mirror P corresponding to a region where the transmittance distribution 85 is equal to or lower than a predetermined transmittance. For example, when the transmittance distribution 85 shown in FIG. 7B is obtained, the control unit 70 removes a minute mirror P (that is, P8, P10 to P16) corresponding to a region showing a transmittance of 50% or less. Switching to the OFF state, the profile of the measurement light is changed to the second profile 200 shown in FIG. For example, the predetermined transmittance may be a preset transmittance (for example, 30% or less, 50% or less, or the like), or a configuration that can be arbitrarily set by the examiner. The control unit 70 may be configured to set based on the transmittance distribution 85.

  At this time, the control unit 70 controls the output of the light source 11 to adjust the amount of measurement light. For example, in FIG. 9, among the 16 minute mirrors P, the four minute mirrors P are in an OFF state, so that the amount of measurement light is ¼ and is irradiated to the eye E. . In this case, for example, the control unit 70 obtains an optimum light amount for the eye E from the area of the irradiation region 110 or the non-irradiation region 120 in the second profile 200 and controls the output of the light source 11. That is, in the case of FIG. 9, the eye E can be optimally illuminated by preliminarily multiplying the output of the light source by four times.

<Acquisition of second OCT data (S8)>
For example, the control unit 70 irradiates the eye E with the measurement light in a state where the profile of the measurement light is changed to the second profile 200, and acquires second OCT data corresponding to the second profile (S8). The second OCT data may be tomographic image data of the eye E, motion contrast data, or polarization characteristic data. For example, the second OCT data may be configured to acquire an OCT signal (that is, a signal before being imaged) or may be configured to acquire an OCT image.

  As described above, for example, the ophthalmologic photographing apparatus according to the present embodiment includes the changing unit that changes the profile of the measurement light and each first OCT in a state where the profile of the measurement light is changed to a plurality of different first profiles. Obtaining means for obtaining data. Further, for example, the ophthalmologic photographing apparatus according to the present embodiment changes the profile of the measurement light to a new second profile different from the first profile as the main photographing profile based on the plurality of OCT data, and the second The second OCT data is acquired with the profile changed. As a result, the examiner tries a plurality of first profiles, and returns the measurement light irradiated on the subject's eye to the fundus and is collected again by the OCT optical system. Can be obtained. The examiner can change the second profile to an optimum profile for the eye to be examined with reference to the information. Therefore, the examiner can acquire OCT data optimized for each eye to be examined.

  In addition, for example, the ophthalmologic photographing apparatus according to the present embodiment includes a light amount adjusting unit that makes the light amount of the measurement light irradiated to the eye to be examined the same in a state where the first profile is changed to a plurality of different first profiles. Thereby, the light quantity in the return light of the measurement light irradiated to the eye to be examined can be easily compared between a plurality of different first profiles. Therefore, the examiner can easily determine a good second profile for the eye to be examined from the result of the first profile.

  For example, the ophthalmologic photographing apparatus according to the present embodiment includes a DMD as the changing unit. For this reason, the profile of the measurement light can be easily changed to various shapes.

<Transformation example>
In this embodiment, a sparse modeling technique may be applied when selecting a plurality of different first profiles 100. In this case, all the first profiles 100 stored in the memory 72 are prioritized, and the first profiles 100 can be selectively changed. Therefore, the control unit 70 can create the transmittance distribution 85 based on a small number of first OCT data. Note that the priority order of the first profile 100 may be changed as needed in the process of creating the transmittance distribution 85.

  In the present embodiment, the case where the irradiation area 110 in the second profile 200 and the irradiation area 110 in the first profile 100 have different areas has been described as an example, but the present invention is not limited to this. For example, the state of the minute mirror P of the DMD 28 may be switched so that the irradiation area 110 in the second profile 200 has the same area as the irradiation area 110 in the first profile 100. For example, in this case, based on the acquired transmittance distribution 85, the area of the irradiation region 110 is reduced by preferentially turning off the minute mirror P corresponding to the position where the transmittance of the measurement light is low. The first profile 100 and the second profile 200 may be the same. In addition, for example, a region where the transmittance of the measurement light is low is wide, and the number of micro mirrors P corresponding thereto exceeds the number of micro mirrors P turned off in the first profile 100. In this case, a minute mirror P to be turned off is determined in consideration of the transmittance around the region where the transmittance of the measurement light is low, and the area of the irradiation region 110 is determined by the first profile 100 and the second profile 200. It may be the same.

  In the present embodiment, the configuration in which the measurement light is locally changed by switching the state of the minute mirror P of the DMD 28 has been described as an example, but the present invention is not limited to this. For example, a member for adjusting the intensity of the measurement light may be arranged in the optical path of the measurement light, and this may be moved or inserted / removed. In this case, an apodization filter may be used as a member for adjusting the intensity of the measurement light, and this may be moved within a plane perpendicular to the measurement light. Further, an LCD (for example, a transmissive LCD, a reflective LCD, or the like) may be used. For example, the eye E may be irradiated with measurement light whose intensity is partially changed in this way.

  For example, when irradiating the eye E with measurement light partially changed in intensity, a continuous value representing the transmittance distribution is adopted as x in the bold body in Equation 1. Therefore, for example, when there is strong dimming only in the position corresponding to the center of the position on the pupil of the eye E (E6, E7, E10, E11), the following formula is obtained, which is described above. Think of it like an example. Similar to Equation 1, after obtaining the simultaneous equations, each component of the transfer matrix may be calculated under assumptions such as sparsity. For example, the control unit 70 may create the transmittance distribution 85 based on this and set the second profile 200.

  In this embodiment, when the first profile 100 is changed, the state of the minute mirror P is switched so that the area of the irradiation region 110 is constant, and the light quantity of the measurement light is the same. Although described above, the present invention is not limited to this. For example, in the present embodiment, the first light profile with different areas of the irradiation region 110 may be set, and the light quantity emitted from the light source 11 may be adjusted to make the light quantity of the measurement light the same. For example, in this case, the control unit 70 changes the amount of measurement light in accordance with the area of the irradiation region 110 in the set first profile 100. For example, the control unit 70 doubles the output of the light source 11 when the area of the irradiation region 110 in the first profile 100 becomes half of the entire area in the first profile 100. As a result, even when the first profile 100 having a different area of the irradiation region 110 is set, the output of the light source 11 can be changed at any time, and the amount of measurement light applied to the eye to be examined can be made the same.

  Further, for example, when the light amount of the measurement light is made the same by adjusting the light amount emitted from the light source 11, the light amount of the measurement light irradiated to the eye E is detected between the DMD 28 and the lens 22a. You may install the photodetector for doing. For example, the control unit 70 may control the output of the light source 11 based on the amount of measurement light detected by the photodetector. In addition, for example, the control unit 70 inserts a member for adjusting the light amount of the measurement light based on the light amount of the measurement light detected by the photodetector in the optical path until the measurement light reaches the eye E to be examined. You may take it off. For example, as a member for adjusting the amount of light, a filter (for example, a density filter, a polarization filter, a neutral density filter, or the like) is used. If a variable density filter is used, it may be fixedly arranged in the optical path until the measurement light reaches the eye E, and rotated or slid to achieve a desired density. For example, even in such a configuration, when the first profile 100 having a different area of the irradiation region 110 is set, the amount of measurement light irradiated to the eye to be examined can be made the same.

  The ophthalmologic photographing apparatus 1 in the present embodiment may be configured to include a photodetector 88 for detecting return light of measurement light. FIG. 10 is a diagram illustrating a modification example in the optical system of the ophthalmologic photographing apparatus 1. For example, in such a case, the beam splitter 87 is provided at any position between the DMD 28 and the lens 22a (between the mirror 29 and the lens 22a in this embodiment), and the measurement reflected by the eye E is measured. The return light is reflected by the beam splitter 87 toward the photodetector 88. For example, the detector 40 may acquire the OCT signal by combining the return light of the measurement light guided to the photodetector 88 and the reference light. For example, the control unit 70 can detect a predetermined signal intensity A from the acquired OCT signal in the same manner as in the present embodiment.

  For example, in the case of the optical system arrangement shown in FIG. 10, the transfer matrix can be similarly obtained by the following formula. Here, 1 of the bold body is a row vector in which all components are 1, and corresponds to a row vector in the case where all the minute mirrors P of the DMD 28 are ON in Equation 1. As with Equation 1, after obtaining the simultaneous equations, each component of the transfer matrix may be calculated with an assumption such as sparsity. For example, the control unit 70 may create the transmittance distribution 85 based on this and set the second profile 200.

  For example, the ophthalmologic photographing apparatus 1 in the present embodiment may include an illumination optical system, a light receiving optical system, and an observation optical system different from the OCT optical system 2. For example, the illumination optical system illuminates the subject eye by emitting irradiation light toward the subject eye. For example, the light receiving optical system receives reflected light from the eye to be examined. For example, the observation optical system acquires a front image of the eye to be examined based on a light reception signal from the light reception optical system. As such an ophthalmologic photographing apparatus 1, the ophthalmic photographing apparatus 1 may be configured to include an SLO or a fundus camera.

  For example, in the ophthalmologic photographing apparatus 1 described above, the control unit 70 changes the profile of the irradiation light in the irradiation optical system. For example, the control unit 70 can change the profile of the irradiation light to the same profile as the second profile. In this case, the DMD 28 may be disposed in a common optical path in the illumination optical system and the measurement optical system 20. In this case, the pattern of the second profile may be arranged on the diaphragm surface of the SLO or the fundus camera. For example, with such a configuration, the profile of the irradiation light in the illumination optical system is changed to the same profile as the second profile of the measurement light.

  For example, as described above, the ophthalmologic photographing apparatus according to the present embodiment includes an illumination optical system that emits irradiation light toward the subject's eye and illuminates the subject's eye, and a light-receiving optical system that receives reflected light from the subject's eye, An observation optical system different from the OCT optical system that acquires a front image of the eye to be inspected based on a light reception signal from the light reception optical system, and a second change unit that changes a profile of irradiation light in the illumination optical system. For this reason, the examiner efficiently refers to the profile of the measurement light acquired in the apparatus equipped with the OCT optical system, and efficiently uses the second profile of the irradiation light in the apparatus equipped with the observation optical system different from the OCT optical system. Can be the same as the profile. In addition, in an apparatus provided with an observation optical system different from the OCT optical system, the eye to be examined can be photographed with high accuracy.

  In the present embodiment, the configuration in which the transmittance distribution 85 for the eye E is created using the predetermined signal intensity A obtained by analyzing all the first OCT data has been described as an example, but the present invention is not limited to this. For example, the transmittance distribution 85 may be created based on the strength of the predetermined signal intensity A determined by the first OCT data. In this case, the transmittance distribution 85 may be created using only the plurality of first OCT data determined to be “strong” or may be created using only the plurality of first OCT data determined to be “weak”. Good. For example, the strength of the predetermined signal intensity A based on the first OCT data can be determined by comparing a predetermined threshold value set in advance by experiment, simulation, or the like with the acquired amplitude intensity. Of course, such a threshold value may be configured to be arbitrarily set by the examiner or may be set every time the subject changes (every eye E changes).

  In the present embodiment, the case where the OCT signal is analyzed as the first OCT data and the predetermined signal intensity A is detected is described as an example, but the present invention is not limited to this. For example, an OCT signal may be analyzed as the first OCT data, and a feature value such as a peak of signal value, contrast, or histogram may be detected. In this case, for example, the first OCT data may be acquired by detecting a rising edge or a falling edge, or may be acquired by cutting out a part of the first OCT data. Of course, it is also possible to analyze the OCT image as the first OCT data and detect the luminance value.

  In the present embodiment, the position of turbidity or the like generated in the eye E may be estimated by using the created transmittance distribution 85. In this case, for example, the control unit 70 may estimate a position where the return light of the measurement light is difficult to transmit at a position on the pupil of the eye E as a position such as turbidity.

DESCRIPTION OF SYMBOLS 1 Ophthalmic imaging device 11 Light source 15 Divider 20 Measurement optical system 22 Light beam diameter adjustment part 23 Condensing position variable optical system 24 Scan part 27 Objective optical system 28 Change member 30 Reference optical system 40 Detector 50 Drive part 70 Control part 100 1st 1 profile 103 measurement unit 200 second profile

Claims (5)

An ophthalmic imaging apparatus that has an OCT optical system that detects an OCT signal generated by measurement light and reference light irradiated on a subject's eye, and that acquires OCT data of the subject's eye by processing the OCT signal,
Changing means for changing the profile of the measurement light in the OCT optical system;
An obtaining means for irradiating the eye to be examined with the measurement light in a state in which the profile of the measurement light is changed to a plurality of different first profiles by the changing means; and acquiring each first OCT data;
With
The changing unit changes the profile of the measurement light as a new imaging profile to a new second profile different from the first profile based on the plurality of OCT data acquired by the acquiring unit,
The acquisition unit is configured to acquire second OCT data by irradiating the eye to be examined with the measurement light in a state in which the second profile is changed. The ophthalmologic photographing apparatus according to claim 1.
An ophthalmologic photographing apparatus comprising: a light amount adjusting unit configured to make the light amounts of the measurement light irradiated to the eye to be examined the same in a state where the first profiles are different from each other. In the ophthalmologic photographing apparatus according to claim 1,
A light receiving signal from the light receiving optical system, comprising: an illumination optical system that emits irradiation light toward the eye to be examined to illuminate the eye to be examined; and a light receiving optical system that receives light reflected from the eye to be examined. An observation optical system for acquiring a front image of the eye to be examined based on the observation optical system different from the OCT optical system,
Second changing means for changing a profile of the irradiation light in the illumination optical system;
With
The ophthalmic imaging apparatus, wherein the second changing means changes the profile of the irradiation light to the same profile as the second profile. In the ophthalmologic photographing apparatus according to any one of claims 1 to 3,
The ophthalmologic photographing apparatus characterized in that the changing means is a DMD. An ophthalmologic imaging method that has an OCT optical system that detects an OCT signal based on measurement light and reference light irradiated on a subject's eye, and acquires OCT data of the subject's eye by processing the OCT signal,
In the state where the profile of the measurement light is changed to a plurality of different first profiles by the changing means for changing the profile of the measurement light in the OCT optical system, the measurement light is irradiated to the eye to be examined. A first acquisition step of acquiring 1OCT data;
A change step of changing the profile of the measurement light to a new second profile different from the first profile as a profile for main imaging based on the plurality of OCT data acquired by the acquisition means;
A second acquisition step of acquiring the second OCT data by irradiating the eye to be examined with the measurement light in the state changed to the second profile;
It is characterized by providing.

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